Preparation and optimization method of long-acting moisture-permeable anti-allergic electrocardio electrode

Abstract

The present application relates to the technical field of computational theoretical chemistry, and particularly relates to a preparation and optimization method of a long-acting moisture-permeable anti-allergic electrocardio electrode, which comprises the following steps: setting electrode-skin interface stability target parameters; calculating the binding energy strength of each candidate polymer material and the skin stratum corneum, and screening the candidate polymer material meeting the allergic reaction probability threshold; constructing a microporous structure model according to the chemical molecular structure of the candidate polymer material, adjusting the micropore gradient distribution parameters until the simulated sweat diffusion rate reaches the sweat diffusion rate threshold; performing dynamic impedance simulation, and when the detection does not reach the impedance decay rate threshold, re-triggering the adjustment of the micropore gradient distribution parameters; and generating and outputting the physical structure parameter set of the electrocardio electrode based on the micropore gradient distribution parameters and the microporous structure model. Through the present application, the problems of insufficient moisture permeability, electrical signal attenuation and skin allergy risk caused by the conflict between sweat diffusion and interface impedance during the material selection and preparation of the existing electrocardio electrode are effectively solved.

Description

Technical Field

[0001] This invention relates to the field of computational theoretical chemistry, and in particular to a method for preparing and optimizing a long-lasting, moisture-permeable, and hypoallergenic electrocardiogram electrode. Background Technology

[0002] Long-lasting, moisture-permeable, and hypoallergenic ECG electrodes are core components for long-term dynamic ECG monitoring, and they must simultaneously meet three core requirements: moisture permeability, electrical signal stability, and biocompatibility. Existing technologies primarily achieve functional optimization through static structural designs such as microporous substrate layers with fixed pore size gradients, isolated material screening, and passive motion adaptation design, but these technologies suffer from serious drawbacks.

[0003] First, static microporous structures cannot respond to the surge in sweat secretion and interfacial impedance fluctuations caused by movement. This leads to a decrease in sweat diffusion rate, causing sweat accumulation and triggering a sharp increase in impedance, creating a positive feedback loop of degradation. Second, the lack of correlation between movement and material deformation characteristics causes the microporous structure to collapse and block connectivity paths under shear force, and there is a lack of self-repair mechanism after impedance degradation exceeds the threshold. Third, the disconnect between material selection and structural design results in insufficient actual moisture permeability of low-allergenic materials due to unreasonable micropore distribution, while the topological changes in the substrate layer caused by movement deformation do not trigger dynamic updates of the adhesive layer components, leading to a rebound in allergy risk. These defects collectively prevent the existing electrodes from achieving synergistic optimization of moisture permeability, electrical stability, and biocompatibility in dynamic environments, severely limiting the reliability of long-term monitoring.

[0004] The information disclosed in this background section is intended only to enhance the understanding of the general background of this disclosure and should not be construed as an admission or in any way implying that the information constitutes prior art known to those skilled in the art. Summary of the Invention

[0005] This invention provides a method for preparing and optimizing a long-lasting, moisture-permeable, and hypoallergenic electrocardiogram electrode, which can effectively solve the problems in the background art.

[0006] To achieve the above objectives, the technical solution adopted by the present invention is as follows:

[0007] A method for preparing a long-lasting, moisture-permeable, and hypoallergenic electrocardiogram electrode, the method comprising:

[0008] Set target parameters for electrode-skin interface stability, including a sweat diffusion rate threshold, an impedance attenuation rate threshold, and an allergic reaction probability threshold.

[0009] Calculate the binding energy strength between each candidate polymer material and the stratum corneum of the skin, and screen the candidate polymer materials whose binding energy strength meets the allergic reaction probability threshold;

[0010] A microporous structure model is constructed based on the chemical molecular structure of the candidate polymer material, and the microporous gradient distribution parameters of the microporous structure model are adjusted until the simulated sweat diffusion rate reaches the sweat diffusion rate threshold.

[0011] Dynamic impedance simulation of the microporous structure model under motion is performed. When the rate of change of interface impedance is detected to be less than the impedance attenuation rate threshold, the adjustment of the microporous gradient distribution parameters is retried.

[0012] The set of physical structure parameters of the ECG electrode is generated and output based on the micropore gradient distribution parameters and the micropore structure model.

[0013] Furthermore, the binding energy strength between each conductive polymer material and the stratum corneum of the skin is calculated, including:

[0014] A biomolecular interface model of the skin stratum corneum was established, which included the spatial configuration and physiological environmental parameters of the lipid bilayer.

[0015] Conformation sampling is performed on the candidate polymer material to obtain the stable spatial conformation set of the candidate polymer material under the constraints of the physiological environmental parameters;

[0016] Based on the stable spatial conformation set and the biomolecular interface interaction model, the change in free energy between the material conformation and the lipid bilayer is calculated according to the perturbation path.

[0017] The quantitative ranking result of the binding energy intensity is generated based on the free energy change value.

[0018] Further, obtaining the stable spatial conformation set of the candidate polymer material under the constraints of the physiological environmental parameters includes:

[0019] The physiological environmental parameter constraints are defined based on the physiological environmental parameters, including thermodynamic fluctuation limits, ion concentration gradients, and pH fluctuation ranges.

[0020] Under the constraints of the physiological environmental parameters, the molecular coordinate space of the candidate polymer material is discretized into a state sequence with energy continuity;

[0021] The molecular potential function is corrected based on the ion concentration gradient, and the conformational energy values ​​of each state sequence are calculated.

[0022] According to the state transition path, the state sequence is traversed, and a subset of conformations whose conformation energy value fluctuation range does not exceed the thermodynamic fluctuation limit and whose conformation centroid spatial distribution variance change rate approaches zero is selected as the stable spatial conformation set.

[0023] Furthermore, a microporous structure model is constructed based on the chemical molecular structure of the candidate polymer material, including:

[0024] Based on the chemical molecular structure, molecular dynamics simulations are performed to generate an initial microporous structure model with a pore topology. The initial microporous structure model is then three-dimensionally meshed to generate a computable microporous structure model carrying the micropore gradient distribution parameters, wherein the micropore gradient distribution parameters are defined as the pore size increasing gradient from the electrode to the skin contact surface towards the environment.

[0025] Furthermore, dynamic impedance simulation of the microporous structure model under motion conditions is performed, including:

[0026] A time-varying diffusion flux of a sweat-sebum mixture is applied to the boundary of the electrode skin contact surface of the microporous structure model.

[0027] A multi-axis motion trajectory is applied to the three-dimensional mesh carrying the microporous structure model, the multi-axis motion trajectory including stretching, torsion and shear components;

[0028] Real-time acquisition of the interface impedance spectrum changes triggered by interface contact pressure fluctuations in the multi-axis motion trajectory;

[0029] When the rate of change of the interface impedance in the interface impedance spectrum exceeds the impedance attenuation rate threshold, an adjustment command for the micropore gradient distribution parameter is generated.

[0030] Furthermore, a time-varying diffusion flux of a sweat-sebum mixture is applied to the boundary of the electrode-skin contact surface of the microporous structure model, including:

[0031] A real-time mapping relationship is established between the kinetic energy intensity of the multi-axis motion trajectory and the sweat secretion rate, wherein the sweat secretion rate increases monotonically with the kinetic energy intensity.

[0032] Configure a monotonically increasing function of sebum percentage with duration of exercise to enable dynamic evolution of the mixed media components;

[0033] The real-time sweat secretion rate and the dynamic composition of the mixed medium are input into the diffusion kinetics model to generate the time-varying diffusion flux with non-steady-state characteristics.

[0034] The time-varying diffusion flux reaches its peak flux at the moment corresponding to the maximum motion intensity.

[0035] Furthermore, the set of physical structural parameters of the ECG electrode includes: the topological features of the gradient microporous substrate layer, the geometric properties of the conductive layer, and the component configuration of the anti-sensitivity adhesive layer.

[0036] A method for optimizing a long-lasting, moisture-permeable, and hypoallergenic electrocardiogram electrode, the method comprising:

[0037] A three-dimensional mesh model is constructed based on the micropore gradient distribution parameters, and a time-varying diffusion flux is loaded onto the electrode skin contact surface boundary of the three-dimensional mesh model;

[0038] The interface impedance spectrum of the three-dimensional mesh model is simulated by coupling multi-axis motion trajectory, and the attenuation conflict coefficient between the interface impedance change rate and the sweat diffusion rate is calculated.

[0039] In response to the attenuation conflict coefficient not being simultaneously lower than the impedance attenuation rate threshold and the sweat diffusion rate threshold, the pore size increment gradient is adjusted to reconstruct the topological features of the gradient microporous substrate layer and update the composition configuration of the anti-sensitivity adhesive layer.

[0040] An optimized set of physical structure parameters is generated when the attenuation conflict coefficient is simultaneously lower than both the impedance attenuation rate threshold and the sweat diffusion rate threshold.

[0041] Furthermore, the attenuation conflict coefficient between the rate of change of interfacial impedance and the sweat diffusion rate is calculated, including:

[0042] Based on the multi-axis motion trajectory data, the motion acceleration vector and the change in skin curvature are analyzed, and the motion disturbance intensity value is obtained by spatial vector coupling calculation.

[0043] Calculate the attenuation ratio of the real-time sweat diffusion rate, and multiply the motion disturbance intensity value by the attenuation ratio to generate a sweat diffusion attenuation factor;

[0044] When the real-time rate of change of the interface impedance exceeds the impedance decay rate threshold, the over-threshold degradation acceleration effect is calculated based on the deformation characteristics of the gradient microporous substrate layer and quantified as an impedance change amplification factor.

[0045] The attenuation conflict coefficient is generated by multiplying the sweat diffusion attenuation factor with the impedance change amplification factor.

[0046] Furthermore, the topological features of the gradient microporous substrate layer are reconstructed and the composition of the anti-sensitivity adhesive layer is updated, including:

[0047] Based on the adjusted pore size increasing gradient, the change in the connectivity path of the gradient micropores in the thickness direction of the substrate layer is calculated, and the pore topology of the gradient micropore substrate layer is reconstructed according to the change.

[0048] The area change rate of the gradient microporous substrate layer surface in contact with the skin after reconstruction is detected, and the relative concentrations of the hydrophilic component and the anti-allergic component of the anti-allergic adhesive layer are adjusted proportionally in response to the area change rate.

[0049] The reconstructed topological parameters of the gradient microporous substrate layer and the updated configuration parameters of the anti-sensitivity adhesive layer components are fed back to the three-dimensional mesh model for model reconstruction.

[0050] The technical solution of this invention can achieve the following technical effects:

[0051] It effectively solves the problems of insufficient moisture permeability, electrical signal attenuation, and skin allergy risk caused by the conflict between sweat diffusion and interface impedance in the material selection and preparation of existing ECG electrodes.

[0052] The above description is only an overview of the technical solution of this application. In order to better understand the technical means of this application and to implement it in accordance with the contents of the specification, and to make the above and other objects, features and advantages of this application more obvious and understandable, the following are specific embodiments of this application. Attached Figure Description

[0053] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0054] Figure 1 A schematic flowchart illustrating a method for preparing a long-lasting, moisture-permeable, and hypoallergenic electrocardiogram electrode;

[0055] Figure 2 A schematic diagram of the process for calculating the binding energy intensity;

[0056] Figure 3 A flowchart illustrating the process of performing dynamic impedance simulation;

[0057] Figure 4 This is a flowchart illustrating an optimized method for a long-lasting, moisture-permeable, and hypoallergenic ECG electrode. Detailed Implementation

[0058] The technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments.

[0059] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains. The terminology used in this specification is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. The term "and / or" as used herein includes any and all combinations of one or more of the associated listed items.

[0060] Example 1;

[0061] like Figure 1As shown, this application provides a method for preparing a long-lasting, moisture-permeable, and hypoallergenic electrocardiogram electrode, the method comprising:

[0062] Set target parameters for electrode-skin interface stability, including sweat diffusion rate threshold, impedance attenuation rate threshold, and allergic reaction probability threshold.

[0063] Calculate the binding energy strength between each candidate polymer material and the stratum corneum of the skin, and screen candidate polymer materials whose binding energy strength meets the allergic reaction probability threshold;

[0064] A microporous structure model was constructed based on the chemical molecular structure of the candidate polymer material, and the microporous gradient distribution parameters of the microporous structure model were adjusted until the simulated sweat diffusion rate reached the sweat diffusion rate threshold.

[0065] Dynamic impedance simulation of the microporous structure model under motion is performed. When the rate of change of interface impedance is not detected to reach the impedance attenuation rate threshold, the adjustment of the microporous gradient distribution parameters is retried.

[0066] The set of physical structure parameters of ECG electrodes is generated and output based on micropore gradient distribution parameters and micropore structure model.

[0067] Specifically, firstly, during electrode fabrication, target parameters for electrode-skin interface stability are set. These target parameters include a sweat diffusion rate threshold, an impedance attenuation rate threshold, and an allergic reaction probability threshold. In a preferred embodiment, the sweat diffusion rate can be measured through skin testing and human simulation experiments. A specific value is selected as the threshold to ensure that the sweat diffusion rate remains stable under dynamic changes without excessive moisture accumulation at the electrode interface. The impedance attenuation rate threshold is established by observing the impedance change under simulated motion of the sample. The preferred condition is to maintain a low impedance change rate under dynamic conditions to ensure signal stability. The allergic reaction probability threshold requires skin allergy testing on multiple individuals, combined with biocompatibility screening. According to the standard, the preferred method is to keep the probability below a certain set value, thereby minimizing the risk of skin sensitivity reactions. Secondly, to achieve the allergic reaction probability threshold in the above target parameters, candidate polymer materials with binding energy strength meeting the requirements of the skin's stratum corneum are screened. In the preferred method, a skin bio-testing data platform can be used to evaluate the binding energy strength of different polymer materials. For example, computer simulations can be used to determine the interaction binding energy between the skin's stratum corneum and material molecules, and this can be verified in conjunction with actual material test results. By screening polymer materials with low allergenicity and high biocompatibility, such as medical-grade siloxane materials or modified polyurethane materials, as candidate materials, the skin affinity performance of the electrode is guaranteed. To improve sweat diffusion performance, a microporous structure model is constructed based on the chemical molecular structures of the selected candidate polymer materials. A preferred approach is to use three-dimensional microstructure design to adjust the gradient distribution parameters of the multi-layered microporous structure, ensuring uniform diffusion of sweat from the skin interface to the electrode. For example, the gradient distribution can be set to gradually decrease from the center of the electrode outwards, forming an efficient channel for liquid diffusion. In a preferred embodiment, the micropore size range can also be adjusted to avoid sweat accumulation due to large pores or breathability issues caused by small pores. In the impedance performance verification section of the microporous structure model, a dynamic simulation analysis method is used in the implementation plan. Based on the power consumption changes at the electrode-skin interface under motion conditions, the impedance change rate is tested to see if it meets the threshold requirements. When the impedance attenuation rate is found to be below the target, the design adjustment of the micropore gradient distribution can be retried, such as adjusting the pore distribution density or pore shape. In a preferred approach, to accelerate the design optimization process, electrochemical testing instruments and dynamic simulation software can be used together to obtain high-precision data feedback. Finally, based on the optimized micropore gradient distribution parameters and micropore structure model, a set of physical structure parameters for the ECG electrode is generated and output. In practice, ECG electrode samples with the set physical parameters are produced through physical processing methods, such as 3D printing or nanofabrication technology. The samples are then subjected to biocompatibility, functional testing, and lifespan testing to ensure their excellent stability, anti-allergy properties, and dynamic performance.

[0068] The technical solution of this invention effectively solves the problems of insufficient moisture permeability, electrical signal attenuation, and skin allergy risk caused by the conflict between sweat diffusion and interface impedance during the material selection and preparation of existing ECG electrodes.

[0069] Furthermore, such as Figure 2 As shown, calculate the binding energy strength between each conductive polymer material and the stratum corneum of the skin, including:

[0070] Establish a biomolecular interface model of the stratum corneum of the skin, which includes the spatial configuration and physiological environmental parameters of the lipid bilayer;

[0071] Conformation sampling is performed on candidate polymer materials to obtain a stable spatial conformation set of candidate polymer materials under physiological environmental parameter constraints;

[0072] Based on the stable spatial conformation set and biomolecular interface interaction model, the free energy change between the material conformation and the lipid bilayer is calculated according to the perturbation path.

[0073] The quantitative ranking of binding energy intensity is generated based on the change in free energy.

[0074] As a preferred embodiment of the above, firstly, to calculate the binding energy strength between the conductive polymer material and the stratum corneum of the skin, a biomolecular interface model of the stratum corneum needs to be established. The model should accurately reflect the biophysical characteristics and interfacial interaction mechanisms of the skin. In a preferred embodiment, the biomolecular interface model of the stratum corneum includes the spatial configuration and physiological environmental parameters of the lipid bilayer. The lipid bilayer can be composed of phospholipid molecules, such as cholesterol and fatty acid molecules, which are mainly present in the stratum corneum. The actual configuration of the cell membrane on the skin surface is simulated using biological data acquisition software and molecular modeling tools. The physiological environmental parameters include key variables such as temperature, humidity, and pH. The optimal settings are those most typical of human skin's physiological environment, such as a temperature of 36-37°C and humidity between 30% and 70%. Next, based on the constructed model, conformational sampling needs to be performed on the candidate polymer materials to obtain a set of stable spatial conformations of the polymer materials under physiological constraints. Preferred conformational sampling methods can employ molecular dynamics simulations, Monte Carlo methods, or large-scale molecular force field calculations to ensure that the conformational samples of the candidate polymer materials in the simulation truly reflect their motion state at the skin interface. By setting simulation runtime, temperature, and humidity constraints, stable conformations of the candidate materials can be further screened out. For example, modified conductive polymer molecules in a weakly acidic environment... The minimum energy configuration was determined, and in specific implementation, experiments were conducted to verify that these materials exhibited good stability and anti-allergic properties in the model environment. After sampling, the binding energy intensity was calculated based on the stable spatial conformation set of the candidate polymer materials and the biomolecular interface interaction model. In a preferred embodiment, the free energy change between the candidate material molecules and the stratum corneum lipid bilayer could be simulated by perturbation paths. Specifically, the free energy calculation module built into molecular dynamics simulation software could be used to simulate the physical interaction energy change between the candidate material molecules and the lipid bilayer during the motion path from the free state to the contact state, and generate the corresponding free energy curve. In a preferred method, the free energy curve could be calculated by setting... The step-by-step sampling density of the perturbation path is determined to ensure the accuracy of the calculation results. Based on the free energy change values ​​mentioned above, a quantitative ranking result of the binding energy intensity needs to be generated. The preferred method is to sort the candidates by binding energy intensity values ​​from high to low after obtaining the free energy change data of all candidate materials, and prioritize the selection of materials with lower binding energy to reduce the risk of skin allergic reactions. In specific implementation, the quantitative ranking of binding energy intensity can not only serve as a basis for material selection, but also further help to verify the biocompatibility of candidate materials. For example, in one embodiment, by calculating the binding energy intensity of medical conductive polypyrrole, it was found that its value was lower than that of traditional conductive polyaniline material, thus determining it as the preferred preparation material with excellent anti-allergic properties.

[0075] Furthermore, obtaining the stable spatial conformation set of candidate polymer materials under physiological environmental parameter constraints includes:

[0076] Physiological environmental parameter constraints are defined based on physiological environmental parameters, including thermodynamic fluctuation limits, ion concentration gradients, and pH fluctuation ranges.

[0077] Under the constraints of physiological environmental parameters, the molecular coordinate space of candidate polymer materials is discretized into a state sequence with energy continuity;

[0078] The molecular potential function is corrected based on the ion concentration gradient, and the conformational energy values ​​of each state sequence are calculated.

[0079] Based on the state transition path, the state sequence is traversed, and a subset of conformations whose conformational energy values ​​fluctuate within the thermodynamic fluctuation limit for multiple consecutive state transitions and whose rate of change of variance of conformational centroid spatial distribution in the state sequence approaches zero is selected as the stable spatial conformation set.

[0080] As a preferred embodiment of the above, firstly, based on the constraints defined by the physiological environment parameters, in a preferred manner, these constraints can be accurately defined by simulating the real physiological environment of human skin. These constraints include thermodynamic fluctuation limits, ion concentration gradients, and pH fluctuation ranges. The thermodynamic fluctuation limits can be determined experimentally by measuring the dynamic change in skin surface temperature over time, for example, setting the fluctuation range to 36℃ ± 0.5℃. The ion concentration gradient can refer to the concentration changes of the main ions in human skin sweat, such as sodium and potassium ions. The pH fluctuation range needs to be set according to the pH changes of the skin surface, generally with a weakly acidic range of 4.5 to 6.5 as the preferred value. This ensures that the physiological environment parameters can accurately reflect the chemical and physical constraints of the candidate material in actual application scenarios. Secondly, under the constraints of the physiological environment parameters, in order to discretize the molecular coordinate space of the candidate polymer material, the molecular coordinate space needs to be divided into states with energy continuity. In a preferred embodiment, molecular dynamics simulation tools can be used to sample the molecular trajectories of candidate materials. By setting a discrete step size, such as 0.1 nanometers, the molecular conformation of the candidate material is divided into multiple discrete spatial states. Each state corresponds to a specific geometric and energy characteristic, facilitating subsequent calculations of conformational energy and centroid distribution variance. In specific implementations, for example, for a conductive polypyrrole material, the conformational changes of its molecular chains under temperature fluctuations and humidity changes can be simulated and discretized into several single states to facilitate subsequent energy calculations and screening. Then, the molecular potential function is corrected based on the ion concentration gradient, and the conformational energy values ​​of each state sequence are calculated. In a preferred embodiment, the biochemical environmental changes caused by skin sweat under the ion concentration gradient can be included in the correction factor of the molecular potential function to improve the accuracy of energy calculations during the conformational process. For example, the ion concentration gradient can be set such that the range of sodium ion gradient variation is limited to 0.1 mol / L to 0.At a concentration of 3 mol / L, the shielding effect directly related to the molecular potential function was calculated using a chemical kinetic model, and the interaction energy of molecules at the skin interface was corrected accordingly. Conformational energy values ​​can be directly extracted using molecular simulation tools, such as generating candidate state sequences from large-scale molecular dynamics data, and analyzing the energy distribution characteristics of each conformation under different physiological environmental parameters. Finally, the state sequence is traversed according to the defined state transition path, and a subset of conformations that meet stability requirements is selected as the final stable spatial conformation set. In a preferred embodiment, this can be achieved through dual constraints on the conformation selection conditions, including that the fluctuation range of the conformational energy value does not exceed the thermodynamic fluctuation limit, and the conformational energy value does not exceed the thermodynamic fluctuation limit. When the rate of change of variance in the centroid spatial distribution of a conformation approaches zero, an automated path traversal algorithm can be used to progressively screen the state transition data at each step, ensuring that the screened conformations possess high stability. For example, during the screening process, if the energy value of a conformation fluctuates within a preset thermodynamic limit across multiple consecutive transitions, and the rate of change of variance in the centroid spatial distribution of these conformations approaches zero (i.e., the centroid position remains almost unchanged), then it is included in the set of stable conformations. In specific implementation, a candidate material, such as medical conductive polyester, can be screened. Its physicochemical stability under temperature fluctuations and humidity changes can be verified through multi-person skin simulation environments to ensure that the screening results meet the design scheme.

[0081] Furthermore, microporous structure models are constructed based on the chemical molecular structure of candidate polymer materials, including:

[0082] Based on the chemical molecular structure, molecular dynamics simulations are performed to generate an initial microporous structure model with a pore topology. The initial microporous structure model is then three-dimensionally meshed to generate a computable microporous structure model carrying micropore gradient distribution parameters, where the micropore gradient distribution parameters are defined as the pore size increasing gradient from the electrode to the skin contact surface towards the environment.

[0083] As a preferred embodiment of the above, firstly, molecular dynamics simulation is performed based on the chemical molecular structure of the candidate polymer material. In a preferred embodiment, molecular dynamics simulation software is used to simulate the conformation of the polymer chain, generating an initial microporous model with actual topological characteristics. This simulation process considers the interaction forces between polymers, such as van der Waals forces and hydrogen bonding, to ensure that the generated pore structure truly reflects the stable configuration of the material in its intrinsic chemical environment. In this step, taking conductive polypyrrole as an example, its chemical molecular structure includes an electron-rich conjugated system and nitrogen atoms that easily form hydrogen bonds. Through simulation, a core pore topology can be generated to guide subsequent structure optimization. Next, the initial microporous structure model is three-dimensionally meshed. Computer-aided design tools can be used to discretize the initial model, dividing it into a detailed three-dimensional mesh structure to ensure the computational accuracy and stability of the model. In specific operations, the preferred method is to select an appropriate... The mesh density parameter and mesh size must be fine enough to capture subtle structural changes in the pores, while also considering the overall computational complexity of the electrode. For example, when meshing is used to characterize the volume change of micropores from the core to the edge, the mesh can be set to cubic units with a side length of about 100 nanometers to balance computational efficiency and detail integrity. Then, a micropore structure model carrying micropore gradient distribution parameters is generated. In a preferred embodiment, when designing the micropore gradient distribution parameters, it is necessary to consider the gradient characteristics of pore size gradually increasing from the inner side of the electrode (i.e., the skin contact surface) to the outer side (i.e., open) to the environment. This can be achieved by dividing the model into multiple layers in the direction perpendicular to the contact surface, with each layer corresponding to a different pore size, thereby precisely controlling the diffusion path and rate of sweat. In a specific example, a method of gradually increasing the pore size can be adopted, that is, setting a smaller pore size at the contact surface, increasing a certain porosity at each layer outward according to a preset gradient, and finally achieving a larger pore size in the outer layer near the environment to achieve the optimal moisture permeability.

[0084] Furthermore, such as Figure 3 As shown, the dynamic impedance simulation of the microporous structure model under motion conditions is performed, including:

[0085] A time-varying diffusion flux of a sweat-sebum mixture was applied to the boundary of the electrode-skin contact surface in the microporous structure model.

[0086] A multi-axis motion trajectory is applied to the three-dimensional mesh supporting the microporous structure model. The multi-axis motion trajectory includes tensile, torsional and shear components.

[0087] Real-time acquisition of interface impedance spectrum changes triggered by interface contact pressure fluctuations in multi-axis motion trajectories;

[0088] When the rate of change of interface impedance in the interface impedance spectrum exceeds the impedance decay rate threshold, an adjustment command for the micropore gradient distribution parameters is generated.

[0089] As a preferred embodiment of the above, firstly, a time-varying diffusion flux of a mixture of sweat and sebum is applied to the boundary of the electrode skin contact surface of the microporous structure model. In a preferred embodiment, the dynamic diffusion behavior of the main components in sweat, such as water, electrolytes, and sebum mixture, should be considered. Diffusion simulation software can be used to accurately simulate the flow and aggregation of these components through the electrode micropores. For example, the change of the diffusion coefficient over time can be set to simulate the fluctuation characteristics of sweat secretion. This setting can provide boundary conditions that are closer to reality for subsequent impedance simulation. Next, a multi-axis motion trajectory is applied to the three-dimensional mesh supporting the microporous structure model. The preferred multi-axis motion trajectory includes tensile, torsional, and shear components. These components can represent different deformations caused by wearer movements such as walking, running, or arm swinging during actual use. Through a motion simulation device, various dynamic parameters are set, such as the periodic strain range of the tensile axis or the frequency of change of the torsional angle, to achieve detailed simulation of each degree of freedom, so as to observe the reliability and durability of the electrode. The process involves several steps. First, during multi-axis motion, the interfacial impedance spectrum changes caused by fluctuations in interfacial contact pressure are collected in real time. This can be achieved using an electrochemical impedance spectroscopy instrument mounted on the electrode model. This instrument records the instantaneous changes in interfacial impedance under motion conditions. For example, it monitors the changes in impedance amplitude and phase between the electrode and skin during flexion and extension, analyzing the response behavior of characteristic peaks in the spectrum with motion. Preferably, the detection accuracy of the fluctuations needs to be set within a high sensitivity range to ensure that signal changes affecting electrode stability and functional performance are captured. Second, when the rate of change in the interfacial impedance spectrum exceeds a preset impedance attenuation rate threshold, the preferred approach is to automatically trigger the control unit after detecting an excessive change in the impedance spectrum. This allows for immediate adjustment of the gradient distribution parameters in the microporous structure model, thereby optimizing its moisture permeability and electrical properties. For instance, if excessive impedance changes are found under a certain motion mode, the gradient can be appropriately controlled by reducing the contact hole diameter or increasing the outer hole diameter, thereby reducing the amplitude of impedance peak fluctuations.

[0090] Furthermore, the time-varying diffusion flux of a sweat-sebum mixture is applied to the electrode-skin contact surface boundary of the microporous structure model, including:

[0091] A real-time mapping relationship between the kinetic energy intensity of a multi-axis motion trajectory and the sweat secretion rate is established, wherein the sweat secretion rate increases monotonically with the kinetic energy intensity.

[0092] Configure a monotonically increasing function of sebum percentage with duration of exercise to enable dynamic evolution of the mixed media components;

[0093] By inputting the real-time sweat secretion rate and the dynamic composition of the mixed medium into the diffusion kinetics model, a time-varying diffusion flux with non-steady-state characteristics is generated.

[0094] The time-varying diffusion flux reaches its peak at the moment corresponding to the maximum motion intensity.

[0095] As a preferred embodiment of the above, firstly, a real-time mapping relationship between the kinetic energy intensity of the multi-axis motion trajectory and the sweat secretion rate is established. In a preferred embodiment, the kinetic energy intensity can be quantified using dynamic motion testing equipment, such as using an accelerometer and velocity sensor to measure the acceleration and instantaneous velocity generated during exercise, and converting them into kinetic energy intensity. According to existing physiological data, the sweat secretion rate and the kinetic energy intensity during exercise have a monotonically increasing relationship, that is, as the exercise intensity increases, the rate of sweat gland secretion increases synchronously. Through experimental data fitting or mechanistic model simulation, an accurate kinetic energy sweat secretion rate mapping curve can be established, for example, the sweat output changes corresponding to mild, moderate, and severe exercise conditions. Secondly, the change in sebum percentage with the duration of exercise is configured as a monotonically increasing function. In a preferred embodiment, as the mixture of media components evolves dynamically, the accumulation of sebum on the skin surface increases with prolonged exercise, thereby altering the relative sebum content in sweat. This change can be quantified by the time curve of sebum secretion under constant exercise conditions and described by a function mapping, such as a low-order polynomial function representing the relationship between sebum proportion and time, in order to predict the change in the proportion of sebum relative to total sweat during prolonged exercise. The subsequent step is to input the real-time sweat secretion rate and the dynamic mixture of media components into the diffusion dynamics model to generate a time-varying diffusion flux with non-steady-state characteristics. In a preferred embodiment, the aforementioned obtained sweat secretion rate mapping function and sebum dynamic evolution function are introduced into the diffusion dynamics simulation to reflect the diffusion behavior of sweat and sebum during actual exercise. This process requires solving the corresponding reaction-diffusion equations to describe the dynamic diffusion gradient of sweat from the interface to the electrode, corresponding to the mixing characteristics of sweat and sebum under different exercise states. Finally, the time-varying diffusion flux reaches its peak at the moment corresponding to the maximum exercise intensity, which is a characteristic covering complex exercise conditions. The moment corresponding to the maximum kinetic energy intensity in the exercise cycle is determined by simulation or experiment, and the maximum sweat flux value at this time is calculated to further adjust and improve the micropore design. This can be achieved by performing time series analysis of diffusion flux during the maximum exercise phase to identify the specific time point when the peak flux occurs, ensuring that the electrode still has stable impedance performance under the most demanding conditions.

[0096] Furthermore, the set of physical structural parameters of the ECG electrodes includes: the topological characteristics of the gradient microporous substrate layer, the geometric properties of the conductive layer, and the composition configuration of the anti-sensitivity adhesive layer.

[0097] As a preferred embodiment of the above, firstly, the topological feature design of the gradient microporous substrate layer, through the optimized design of the microporous geometry, achieves efficient permeability of moisture and sweat. In a preferred embodiment, a polymer material with hydrophilicity and biodegradability, such as modified polyurethane or siloxane, can be selected as the substrate material. A gradient distribution is achieved by precisely controlling the size and shape of the micropores. The topological features of the microporous layer can include a longitudinal gradient of pore size variation, i.e., the pore size gradually changes from the inner to the outer side of the electrode, increasing from the inside to the outside to optimize moisture channels. For example, the pore size inside the electrode is set to 3 micrometers, while it increases to 12 micrometers on the outside to meet the needs of dynamic sweat transmission. In specific operations, these gradient pore structures are precisely manufactured using nanomolding technology or 3D printing technology to ensure that the porosity and distribution meet the design requirements. Secondly, in a preferred embodiment of the selection of the geometric properties of the conductive layer, a material with good conductivity, high flexibility, and resistance to corrosion can be selected, such as silver nanowires or conductive... Polymer nanocomposites, used as the substrate for the conductive layer, require careful consideration of surface smoothness and thickness in their design to ensure good conductivity and anti-interference capabilities during skin adhesion. In practice, sputtering coating technology or conductive ink printing can be used to achieve a skin-fitting conductive layer structure. Typically, the conductive layer thickness is controlled within 10 micrometers to optimize electrode conductivity and comfort. Finally, the optimal selection of components for the anti-allergenic adhesive layer combines hypoallergenic, biocompatible, and high-adhesion adhesive materials, such as medical adhesives and modified acrylic polymers. In practice, adjusting the adhesive's molecular structure, such as adding ester groups or modifying hydroxyl groups, can enhance its skin affinity and reduce the likelihood of allergic reactions. To ensure sustained adhesion, a breathable film can be added to the outer surface of the adhesive layer to control moisture permeability, thus ensuring both strong adhesion and support for natural skin respiration during application.

[0098] Example 2;

[0099] like Figure 4 As shown, this application provides an optimized method for a long-lasting, moisture-permeable, and hypoallergenic electrocardiogram electrode, the method comprising:

[0100] A three-dimensional mesh model is constructed based on the micropore gradient distribution parameters, and a time-varying diffusion flux is loaded onto the electrode skin contact surface boundary of the three-dimensional mesh model;

[0101] The interface impedance spectrum of a three-dimensional mesh model is simulated by coupling multi-axis motion trajectories, and the attenuation conflict coefficient between the interface impedance change rate and the sweat diffusion rate is calculated.

[0102] When the attenuation conflict coefficient is not simultaneously lower than the impedance attenuation rate threshold and the sweat diffusion rate threshold, the pore size increment gradient is adjusted to reconstruct the topological features of the gradient microporous substrate layer and update the composition configuration of the anti-sensitivity adhesive layer.

[0103] An optimized set of physical structure parameters is generated when the attenuation conflict coefficient is simultaneously lower than both the impedance attenuation rate threshold and the sweat diffusion rate threshold.

[0104] Specifically, firstly, a three-dimensional mesh model is constructed based on the micropore gradient distribution parameters, and a time-varying diffusion flux is applied to the electrode-skin contact surface boundary of the three-dimensional mesh model. Specifically, the construction of the three-dimensional mesh model should be centered on the electrode micropore gradient distribution. The micropore layer is discretized according to the actually selected gradient increment parameters, with a preferred mesh size of 0.1 to 2 micrometers to accurately capture the detailed features of the electrode microstructure and provide a precise geometric description for diffusion calculations. Subsequently, when applying the time-varying diffusion flux to the skin contact surface boundary, the secretion patterns of human sweat glands can be combined with the concentration gradient of the mixed medium of sweat and sebum and its change over time to simulate the dynamic diffusion matrix under real-world usage conditions. The sweat secretion rate and diffusion curve are designed to exhibit significant peak behavior during short-duration high-intensity exercise phases to reflect diffusion characteristics in real-world environments. Secondly, multi-axis motion trajectory data is coupled to simulate the interfacial impedance spectrum, and the attenuation conflict coefficient between the interfacial impedance change rate and the sweat diffusion rate is calculated. In the preferred embodiment, the multi-axis motion trajectory data should incorporate the actual state of the electrodes under dynamic wear, including local deformations such as stretching, torsion, and shearing. Under such dynamic load conditions, the changes in the electrode-skin interfacial impedance spectrum are generated in real time using finite element analysis combined with electrochemical impedance simulation technology. Significant changes in the spectrum are used as the basis for calculating the impedance change rate. Simultaneously, the interfacial diffusion rate is calculated using a diffusion model. The flux is analyzed, and its decay over time is extracted. Combined with the aforementioned impedance change rate, the decay conflict coefficient is calculated as a constraint optimization index to ensure that the electrode maintains impedance stability while maximizing the moisture permeability rate. When the decay conflict coefficient is found not to be lower than both the impedance decay rate threshold and the sweat diffusion rate threshold simultaneously, the optimization tool automatically triggers an instruction to adjust the pore size gradient, redesigning the topological characteristics of the gradient microporous substrate layer. Specific adjustments may include increasing the initial pore size, increasing the gradient, or enhancing pore regularity to avoid uneven diffusion. Simultaneously, the composition configuration of the anti-allergy adhesive layer is further optimized based on the anti-allergy properties of the adhesive layer material, such as appropriately introducing a suitable amount of compatible ingredients with anti-inflammatory effects, like... Plant polyols or low molecular weight hydrophilic and skin-friendly materials further reduce the probability of skin sensitivity reactions. When the attenuation conflict coefficient is lower than both the impedance attenuation rate threshold and the sweat diffusion rate threshold after adjustment, an optimized set of physical structure parameters can be generated. This set of structural parameters includes the topological parameters of the gradient microporous substrate, such as the pore size gradient range and distribution uniformity, the geometric parameters of the conductive layer, such as the film thickness and coverage uniformity, and the detailed composition ratio of the adhesive layer. To verify the effectiveness of the optimization results, tests can be conducted by simulating long-term wear and use scenarios to ensure that it can still provide stable signal acquisition performance and skin comfort under human sweat environment and exercise load conditions.

[0105] Furthermore, the calculation of the attenuation conflict coefficient between the rate of change of interfacial impedance and the sweat diffusion rate includes:

[0106] Based on multi-axis motion trajectory data, the motion acceleration vector and the change in skin curvature are analyzed, and the motion disturbance intensity value is obtained by spatial vector coupling calculation.

[0107] Calculate the attenuation ratio of the real-time sweat diffusion rate, and multiply the motion disturbance intensity value by the attenuation ratio to generate the sweat diffusion attenuation factor;

[0108] When the real-time rate of change of interfacial impedance exceeds the threshold of impedance decay rate, the over-threshold degradation acceleration effect is calculated based on the deformation characteristics of the gradient microporous substrate layer and quantified as an impedance change amplification factor.

[0109] The attenuation conflict coefficient is generated by multiplying the sweat diffusion attenuation factor with the impedance change amplification factor.

[0110] As a preferred embodiment of the above, firstly, based on the multi-axis motion trajectory data, the motion acceleration vector and the change in skin curvature are analyzed. The motion acceleration vector can be obtained by collecting sensor data on the user's dynamic behavior, for example, by installing a triaxial accelerometer on the person wearing the electrodes to record the acceleration changes in three dimensions in real time. These data are combined with the change in skin curvature through spatial vector analysis to simulate the degree of deformation of the skin contact interface during movement. For example, during running or strenuous exercise, the change in skin curvature increases significantly due to joint movement, and its spatial coupling with the acceleration vector can reflect the amplitude characteristics of the motion disturbance intensity value. In a preferred embodiment, the regression of the disturbance intensity value can be set. A range is defined to quantify the impact of exercise on sweat diffusion in subsequent calculations. Then, the attenuation ratio of the real-time sweat diffusion rate is calculated, and the exercise disturbance intensity value is multiplied by this attenuation ratio to generate a sweat diffusion attenuation factor. The preferred method for determining the sweat diffusion rate attenuation ratio can be combined with a dynamic diffusion model, recording data in real-time based on sweat gland secretion characteristics and sebum dynamic accumulation behavior. For example, in the later stages of high-intensity exercise, the diffusion rate decreases due to sebum covering sweat diffusion channels; this effect can be represented by the attenuation slope in the time-diffusion curve. When the exercise disturbance intensity value is high, dynamic skin deformation further compresses pore size or changes diffusion directionality, thereby amplifying the attenuation characteristics of the diffusion rate. These factors... After coupling calculation, a real-time sweat diffusion attenuation factor can be generated, thus accurately reflecting the degree of weakening of diffusion characteristics under dynamic conditions. Next, when the real-time interface impedance change rate exceeds the impedance attenuation rate threshold, the over-threshold degradation acceleration effect is calculated based on the deformation characteristics of the gradient microporous substrate layer and quantified as an impedance change amplification factor. In a preferred embodiment, the deformation distribution of the gradient microporous substrate layer is simulated using the finite element method, and the additional impedance fluctuation caused by deformation is solved by combining the elastic modulus of the material and the film thickness. For example, when the pore size of the microporous structure changes significantly due to stretching, compression, or shearing, it will lead to a redistribution of the contact area between the interface electrode liquid electrolyte and the conductive layer, thereby significantly increasing the dynamic impedance wave. The accelerated degradation effect beyond the threshold is quantified by extracting the coupling relationship between impedance change rate and deformation. In the preferred implementation, this factor can be experimentally measured to confirm that it can effectively delineate the degradation mode of electrode performance under high deformation. Finally, the sweat diffusion attenuation factor is multiplied by the impedance change amplification factor to generate the attenuation conflict coefficient. The calculation of these two types of characteristics can not only comprehensively reflect the conflict relationship between diffusion and impedance characteristics, but also provide a clear objective function value for optimizing electrode design. When the conflict coefficient is too high, it indicates that the existing micropore design or adhesive layer configuration cannot meet the balance requirements under dynamic motion conditions. This provides a basis for the adjustment of statistical thresholds for subsequent optimization steps.

[0111] Furthermore, reconstructing the topological features of the gradient microporous substrate layer and updating the composition configuration of the anti-sensitivity adhesive layer includes:

[0112] Based on the adjusted pore size increasing gradient, the change in the connectivity path of the gradient micropores in the thickness direction of the substrate layer is calculated, and the pore topology of the gradient micropore substrate layer is reconstructed according to the change.

[0113] The area change rate of the gradient microporous substrate layer surface in contact area with the skin after reconstruction was detected, and the relative concentrations of the hydrophilic component and the anti-allergic component of the anti-allergic adhesive layer were adjusted proportionally in response to the area change rate.

[0114] The topological parameters of the reconstructed gradient microporous substrate layer and the updated configuration parameters of the anti-sensitivity adhesive layer are fed back into the 3D mesh model for model reconstruction.

[0115] As a preferred embodiment of the above, firstly, based on the adjusted pore size increment gradient, the change in the connectivity path of the gradient micropores in the thickness direction of the substrate layer is calculated. By performing three-dimensional structural analysis of the gradient micropores, it is possible to accurately measure how the pore size change in the material thickness direction affects the topology of the connectivity path. For example, as the micropore size increases from the inside to the outside, the continuous expansion of the connectivity path is set as the target to ensure that the impact of the pore size increment on the flow channel is finely controlled. Through microstructure modeling software, such as finite element analysis or three-dimensional microscopic imaging, the connectivity, total porosity, and flow resistance of the microporous network are optimized and simulated. In specific operation, the optimization of the connectivity path can ensure smoother flow of sweat and gas between the electrode surface and the deep layer, thereby improving the overall moisture permeability of the electrode. Next, the rate of change of the area of ​​the microporous substrate layer surface in contact with the skin after reconstruction is detected. In a preferred embodiment, the contact area can be measured in a precise simulated wearing scenario using a contact angle measuring instrument and a skin simulation system. The change in the surface contact area after reconstruction is normalized. To facilitate further adjustment of the hydrophilicity and anti-allergy component ratio of the anti-allergy adhesive layer, for example, larger contact areas require increasing the hydrophilic components, such as adding more hydrophobic segments like polyethylene glycol, to enhance rapid moisture conduction and reduce skin irritation. Based on actual measurement data and the rate of change of contact area, the chemical composition of the adhesive is adjusted accordingly to ensure a high level of biocompatibility and mechanical stability during dynamic movement. Finally, the topological parameters of the reconstructed gradient microporous substrate layer and the updated anti-allergy adhesive layer component configuration parameters are fed back to the three-dimensional mesh model for model reconstruction. In this process, the aforementioned updated topological and chemical parameters are integrated into the mesh-based static and dynamic analytical models to verify its comprehensive performance in terms of electrical impedance, moisture permeability, and anti-allergy efficacy under simulated long-term wear conditions. Through multiple iterative calculations and optimizations in the model, the complete synergistic work of the microporous structure and adhesive layer is ensured. Specifically, this adjustment and reconstruction process can be quickly fed back to the design database to improve the physical prototype and ensure the implementation and mass production adaptability of the new material design scheme.

[0116] Although this application has been described in conjunction with specific features and embodiments, it is obvious that various modifications and combinations can be made thereto without departing from the spirit and scope of this application. Accordingly, this specification and drawings are merely exemplary illustrations of the application as defined herein, and are to be considered as covering any and all modifications, variations, combinations, or equivalents within the scope of this application. Clearly, those skilled in the art can make various alterations and modifications to this application without departing from its scope. Thus, if such modifications and modifications fall within the scope of this application and its equivalents, this application intends to include such modifications and modifications.

Claims

1. A method for preparing a long-lasting, moisture-permeable, and hypoallergenic electrocardiogram electrode, characterized in that, The method includes: Set target parameters for electrode-skin interface stability, including a sweat diffusion rate threshold, an impedance attenuation rate threshold, and an allergic reaction probability threshold. Calculate the binding energy strength between each candidate polymer material and the stratum corneum of the skin, and screen the candidate polymer materials whose binding energy strength meets the allergic reaction probability threshold; A microporous structure model is constructed based on the chemical molecular structure of the candidate polymer material, and the microporous gradient distribution parameters of the microporous structure model are adjusted until the simulated sweat diffusion rate reaches the sweat diffusion rate threshold. Dynamic impedance simulation of the microporous structure model under motion is performed. When the rate of change of interface impedance is detected to be less than the impedance attenuation rate threshold, the adjustment of the microporous gradient distribution parameters is retried. The set of physical structure parameters of the ECG electrode is generated and output based on the micropore gradient distribution parameters and the micropore structure model.

2. The method for preparing the long-lasting, moisture-permeable, and anti-allergic ECG electrode according to claim 1, characterized in that, Calculate the binding energy strength between each conductive polymer material and the stratum corneum of the skin, including: A biomolecular interface model of the skin stratum corneum was established, which included the spatial configuration and physiological environmental parameters of the lipid bilayer. Conformation sampling is performed on the candidate polymer material to obtain the stable spatial conformation set of the candidate polymer material under the constraints of the physiological environmental parameters; Based on the stable spatial conformation set and the biomolecular interface interaction model, the change in free energy between the material conformation and the lipid bilayer is calculated according to the perturbation path. The quantitative ranking result of the binding energy intensity is generated based on the free energy change value.

3. The method for preparing the long-lasting, moisture-permeable, and anti-allergic ECG electrode according to claim 2, characterized in that, Obtaining the stable spatial conformation set of the candidate polymer material under the constraints of the physiological environmental parameters includes: The physiological environmental parameter constraints are defined based on the physiological environmental parameters, including thermodynamic fluctuation limits, ion concentration gradients, and pH fluctuation ranges. Under the constraints of the physiological environmental parameters, the molecular coordinate space of the candidate polymer material is discretized into a state sequence with energy continuity; The molecular potential function is corrected based on the ion concentration gradient, and the conformational energy values ​​of each state sequence are calculated. According to the state transition path, the state sequence is traversed, and a subset of conformations whose conformation energy value fluctuation range does not exceed the thermodynamic fluctuation limit and whose conformation centroid spatial distribution variance change rate approaches zero is selected as the stable spatial conformation set.

4. The method for preparing the long-lasting, moisture-permeable, and anti-allergic ECG electrode according to claim 1, characterized in that, Constructing a microporous structure model based on the chemical molecular structure of the candidate polymer material includes: Based on the chemical molecular structure, molecular dynamics simulations are performed to generate an initial microporous structure model with a pore topology. The initial microporous structure model is then three-dimensionally meshed to generate a computable microporous structure model carrying the micropore gradient distribution parameters, wherein the micropore gradient distribution parameters are defined as the pore size increasing gradient from the electrode to the skin contact surface towards the environment.

5. The method for preparing the long-lasting, moisture-permeable, and anti-allergic ECG electrode according to claim 1, characterized in that, The dynamic impedance simulation of the microporous structure model under motion conditions includes: A time-varying diffusion flux of a sweat-sebum mixture is applied to the boundary of the electrode skin contact surface of the microporous structure model. A multi-axis motion trajectory is applied to the three-dimensional mesh carrying the microporous structure model, the multi-axis motion trajectory including stretching, torsion and shear components; Real-time acquisition of the interface impedance spectrum changes triggered by interface contact pressure fluctuations in the multi-axis motion trajectory; When the rate of change of the interface impedance in the interface impedance spectrum exceeds the impedance attenuation rate threshold, an adjustment command for the micropore gradient distribution parameter is generated.

6. The method for preparing the long-lasting, moisture-permeable, and anti-allergic ECG electrode according to claim 5, characterized in that, The time-varying diffusion flux of a sweat-sebum mixture is applied to the electrode-skin contact surface boundary of the microporous structure model, including: A real-time mapping relationship is established between the kinetic energy intensity of the multi-axis motion trajectory and the sweat secretion rate, wherein the sweat secretion rate increases monotonically with the kinetic energy intensity. Configure a monotonically increasing function of sebum percentage with duration of exercise to enable dynamic evolution of the mixed media components; The real-time sweat secretion rate and the dynamic composition of the mixed medium are input into the diffusion kinetics model to generate the time-varying diffusion flux with non-steady-state characteristics. The time-varying diffusion flux reaches its peak flux at the moment corresponding to the maximum motion intensity.

7. The method for preparing the long-lasting, moisture-permeable, and anti-allergic ECG electrode according to claim 1, characterized in that, The set of physical structural parameters of the ECG electrode includes: the topological features of the gradient microporous substrate layer, the geometric properties of the conductive layer, and the component configuration of the anti-sensitivity adhesive layer.

8. An optimized method for long-lasting, moisture-permeable, and anti-allergic ECG electrodes, characterized in that, The method includes: A three-dimensional mesh model is constructed based on the micropore gradient distribution parameters, and a time-varying diffusion flux is loaded onto the electrode skin contact surface boundary of the three-dimensional mesh model; The interface impedance spectrum of the three-dimensional mesh model is simulated by coupling multi-axis motion trajectory, and the attenuation conflict coefficient between the interface impedance change rate and the sweat diffusion rate is calculated. In response to the attenuation conflict coefficient not being simultaneously lower than the impedance attenuation rate threshold and the sweat diffusion rate threshold, the pore size increment gradient is adjusted to reconstruct the topological features of the gradient microporous substrate layer and update the composition configuration of the anti-sensitivity adhesive layer. An optimized set of physical structure parameters is generated when the attenuation conflict coefficient is simultaneously lower than both the impedance attenuation rate threshold and the sweat diffusion rate threshold. The calculation of the attenuation conflict coefficient between the rate of change of interfacial impedance and the sweat diffusion rate includes: Based on the multi-axis motion trajectory data, the motion acceleration vector and the change in skin curvature are analyzed, and the motion disturbance intensity value is obtained by spatial vector coupling calculation. Calculate the attenuation ratio of the real-time sweat diffusion rate, and multiply the motion disturbance intensity value by the attenuation ratio to generate a sweat diffusion attenuation factor; When the real-time rate of change of the interface impedance exceeds the impedance decay rate threshold, the over-threshold degradation acceleration effect is calculated based on the deformation characteristics of the gradient microporous substrate layer and quantified as an impedance change amplification factor. The attenuation conflict coefficient is generated by multiplying the sweat diffusion attenuation factor with the impedance change amplification factor.

9. The method for optimizing long-lasting, moisture-permeable, and anti-allergic ECG electrodes according to claim 8, characterized in that, The topological features of the gradient microporous substrate layer are reconstructed and the composition of the anti-sensitivity adhesive layer is updated, including: Based on the adjusted pore size increasing gradient, the change in the connectivity path of the gradient micropores in the thickness direction of the substrate layer is calculated, and the pore topology of the gradient micropore substrate layer is reconstructed according to the change. The area change rate of the gradient microporous substrate layer surface in contact with the skin after reconstruction is detected, and the relative concentrations of the hydrophilic component and the anti-allergic component of the anti-allergic adhesive layer are adjusted proportionally in response to the area change rate. The reconstructed topological parameters of the gradient microporous substrate layer and the updated configuration parameters of the anti-sensitivity adhesive layer components are fed back to the three-dimensional mesh model for model reconstruction.

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